Biological data measurement device

ABSTRACT

A biological data measurement device in which a living organism having a first thermal resistance Rth 1  from a core to a surface is a measuring object, includes a heat insulating layer which is disposed on a body surface of the measuring object and has a second thermal resistance Rth 2 ; a measurement device for measuring a first and a second temperatures, which is segregated by the heat insulating layer; and an adding device for adding a predetermined delay time to the second temperature in order to correct a response delay of the first temperature as compared with the second temperature. The first temperature is a bottom side temperature of a bottom surface of the heat insulating layer, which is in contact with the body surface, and the second temperature is a top side temperature of a top surface of the heat insulating layer.

CROSS-REFERENCE TO RELATED APPLICATION

This is a divisional application of Ser. No. 16/201,462 filed on Nov.27, 2018, which claims priority of Japanese Patent Application No.2017-231112 filed on Nov. 30, 2017, the disclosure of which isincorporated herein as a reference.

TECHNICAL FIELD

The present invention relates to an object data measurement device,especially a biological data measurement data device attached onto abody surface of a living organism to measure biological data. Inparticular, the present invention relates to a biological datameasurement device for measuring especially a deep body temperature ofthe living organism.

BACKGROUND

At the present time, a single-heat-flux (SHF) method, a dual-heat-flux(DHF) method, and a zero-heat-flux (ZHF) method are known as a methodfor measuring a deep body temperature by attaching a device onto a bodysurface of a living organism.

FIG. 29 shows a configuration of FIG. 2 described in Patent Reference 1(WO 2011/012386A) as one example of the single-heat-flux (SHF) method.In FIG. 29 , a reference number 2 indicates a first probe, 6 indicates asecond probe, 4 indicates a heat insulating material, and 3 indicates abody surface. A heat flow (heat flux) generated substantiallyperpendicular to the body surface 3 is measured by the first probe 2 andthe second probe 6.

The SHF method has advantages that a heater is not required and thus asimple configuration is advantageously implemented with a lower powerconsumption, but has a disadvantage that the measurement is likely totake about 10 minutes. Additionally, it is necessary to measure athermal resistance (in vivo thermal resistance) in the living organismby another method in advance.

FIG. 30 shows a configuration of FIG. 1 described in Patent Reference 2(JP S63-058223 A) as one example of the dual-heat-flux (DHF) method. InFIG. 30 , reference numbers 11 and 17 indicate a pair of firsttemperature sensors, while 12 and 18 indicate a pair of secondtemperature sensors. A deep body temperature of a living organism ismeasured based on a heat flow measured by the pair of first temperaturesensors 11, 17 and a heat flow measured by the pair of the secondtemperature sensors 12, 18.

The DHF method has advantageous effects that the deep body temperaturecan be acquired without measuring an in vivo thermal resistance byanother method, and a heater is not required and thus the powerconsumption is low. However, the measurement also takes about 10minutes, and two pairs of temperature sensors are needed.

FIG. 31 shows a configuration of FIG. 6 described in Patent Reference 3(US 2016/0238463 A) as one example of the zero-heat-flux (ZHF) method.In FIG. 31 , a reference number 140 indicates a temperature sensor, and126 indicates a heater.

According to the ZHF method, the temperature sensor 140 affixed onto askin surface is heated by the heater 126, and a deep body temperature isdisplayed on a display when the temperature sensor 140 and the deep bodytemperature reach equilibrium (it takes about 3 minutes).

As described above, the ZHF method has an advantage that the measurementtakes a relatively short time, e.g. about 3 minutes, but on the otherhand, has a disadvantage that the power consumption of the heater isabout 1 W (watt).

Since the ZHF method needs the power consumption of about 1 W, it isdifficult to apply the ZHF method to a bandage-type sensor used by beingadhered to the body surface.

Regarding wirings around the sensor, four wirings are required even forthe SHF method, while eight wirings are required for the DHF method.These wirings are needed to be connected to a single reading circuit orthe like, thus it takes a lot of trouble.

Heat conduction in a horizontal direction (a direction substantiallyparallel to the body surface) by the wiring causes sensitivitydeterioration and device faults. Furthermore, the device is connected todata collection equipment via the wiring, thus it takes time to attachthe device onto the living organism and wearing device is a kind ofburden.

Moreover, the SHF method has advantages that a heater is not requiredand thus a simple configuration is advantageously implemented with alower power consumption, but has a disadvantage that it is necessary tomeasure a thermal resistance (in vivo thermal resistance) in the livingorganism by another method in advance.

SUMMARY

A first object of the present invention is to provide a biological datameasurement device which has a simple configuration, excellentwearability to a body surface of a living organism, and is capable ofaccurately measuring, in particular, a deep body temperature.

A second object of the present invention is to provide a measurementdevice, in particular, a biological data measurement device which adoptsthe SHF method as having a single temperature measurement unit, and iscapable of obtaining a deep body temperature without measuring an invivo thermal resistance of a measuring object by another unit.

The present invention includes a first invention for achieving the firstobject and a second invention for achieving the second object.

For achieving the first object, a biological data measurement deviceaccording to the first invention, includes a substrate disposed at aposition spaced a predetermined distance from a body surface of a livingorganism as a measuring object via a support member so that an air layeris formed between the substrate and the body surface. The substrate isprovided with a thermometer including an infrared thermometer formeasuring a body surface temperature of the body surface and a substratethermometer for measuring a substrate temperature of the substrate.

It is preferable that the infrared thermometer is provided with acalibration thermometer, and the calibration thermometer is used for thesubstrate thermometer.

The support member is made of a heat insulating material and forms asubstantially sealed space as the air layer between the infraredthermometer and the body surface. It is preferable that a foamed plasticmaterial is used as the heat insulating material.

It preferable that the infrared thermometer is provided on a lowersurface side of the substrate, opposing to the body surface, and thesubstrate is the covered with the heat insulating material at a portionother than the air layer, including an upper surface thereof.

In another aspect, the infrared thermometer may be provided on a lowersurface side of the substrate, opposing to the body surface, and theheat insulating material may be disposed as a cylindrical body on thelower surface side of the substrate so as to surround the air layer.

In the first invention, the substrate is provided with a transmitterwhich wirelessly transmits a body surface temperature measured by theinfrared thermometer and a substrate temperature measured by thesubstrate thermometer.

As the substrate is provided with the transmitter, the substrate isaccommodated in a case at least partially having an electromagnetic wavetransmission region in a state where the substrate is supported by theheat-insulating material.

In the first invention, the case may include a box body of which abottom surface on a body surface side is open, and which has a top plateand a side plate bent downward at a substantially right angle from aperipheral edge of the top plate, the bottom surface may be entirelycovered with a sheet, and an adhesive gel may be applied on a bodysurface side of the sheet.

The sheet and the adhesive gel may be made of an infrared-transparentmaterial.

In the first invention, the case may be provided with a box-shaped casebody of which a top surface is open and which has a bottom plate and aside plate bent upward at a substantially right angle from a peripheraledge of the bottom plate; and a lid which detachably covers the topsurface of the case body.

In the first invention, a high thermal conductive film is provided inthe case in order to transmit heat entering into and leaving from a sideplate side.

The biological data measurement device according to the first inventionincludes a calculator. When the body surface temperature is Tsk, thesubstrate temperature is Tsub, a thermal resistance of the air layer isRthair, and a heat flow that flows substantially perpendicular to thebody surface is Ith, the calculator obtains the heat flow Ith from anequation (Tsk−Tsub)/Rthair.

When a thermal resistance from a deep tissue to the body surface in theliving organism is Rthbody and a deep body temperature of the livingorganism is Tcore, the calculator obtains the deep body temperatureTcore from an equation Tsk+Ith×Rthbody.

In the first invention, the biological data measurement device mayinclude in vivo electrical resistance measurement means for measuring anelectrical resistance in the living organism. The thermal resistanceRthbody may be estimated from an in vivo electrical resistance valuemeasured by the in vivo electrical resistance measurement means.

In the biological data measurement device according to another aspect, afirst thermometer and a second thermometer are disposed in parallel onthe substrate, as the thermometer. The first thermometer includes afirst infrared thermometer for measuring a body surface temperature ofthe body surface and a first substrate thermometer for measuring asubstrate temperature of the substrate. The second thermometer includesa second infrared thermometer for measuring a body surface temperatureof the body surface and a second substrate thermometer for measuring asubstrate temperature of the substrate. The upper surface of thesubstrate, on which the first thermometer is disposed, is covered withthe heat insulating material.

The biological data measurement device according to another aspectincludes a calculator for obtaining a deep body temperature Tcore of theliving organism. When the body surface temperature measured by the firstthermometer is Tsk1, a heat flow that flows substantially perpendicularto the body surface is Ith1, the body surface temperature measured bythe second thermometer is Tsk2, a heat flow that flows substantiallyperpendicular to the body surface is Ith2, a thermal resistance from adeep tissue to the body surface in the living organism is Rthbody, thecalculator calculates Rthbody from an equation (Tsk2−Tsk1)/(Ith1−Ith2)and then obtains the deep body temperature Tcore of the living organismfrom an equation (Ith1×Rthbody+Tsk1) or (Ith2×Rthbody+Tsk2).

For achieving the second object, the second invention encompassesseveral aspects as described below.

In an object data measurement device according to a first aspect of thesecond invention, an object having a first thermal resistance Rth1 froma core to a surface is a measuring object. The object data measurementdevice includes a heat insulating layer which is disposed on a bodysurface of the measuring object and has a second thermal resistanceRth2; measurement means for measuring a first and a second temperatures,which is segregated by the heat insulating layer; calculation means forcalculating the first thermal resistance based on the first and thesecond temperatures measured at a first timing A, and the first and thesecond temperatures measured at a second timing B after a predeterminedtime has elapsed from the first timing A; and calculation means forcalculating a deep body temperature of the measuring object based on thefirst and the second thermal resistances, and the first and the secondtemperatures.

According to a second aspect of the second invention, the object datameasurement device includes calculation means for calculating the firstthermal resistance Rth1 from an equation Rth2×b/(a−b) when a differencebetween the first temperatures measured at the first timing A andmeasured at the second timing B is a, a difference between the secondtemperatures measured at the first timing A and measured at the secondtiming B is b, and the second thermal resistance is Rth2.

According to a third aspect of the second invention, the object datameasurement device includes calculation/change means for calculating adeep body temperature TcoreA of the measuring object at the first timingA and a deep body temperature TcoreB of the measuring object at thesecond timing B based on a temporary value set as the first thermalresistance Rth1, and for changing a value of the first thermalresistance Rth1 so that an absolute value obtained by subtracting thedeep body temperature TcoreB from the deep body temperature TcoreA fallswithin a predetermined determination value range.

According to a fourth aspect of the second invention, the firsttemperature is a bottom side temperature of a bottom surface of the heatinsulating layer, which is in contact with an object surface, the secondtemperature is a top side temperature of a top surface of the heatinsulating layer, and the object data measurement device furtherincludes adding means for adding a predetermined delay time to thesecond temperature in order to correct a response delay of the firsttemperature as compared with the second temperature.

According to a fifth aspect of the second invention, a biological datameasurement device includes a substrate disposed at a position spaced apredetermined distance from a body surface of a living organism as ameasuring object via a support member so that an air layer is formedbetween the substrate and the body surface. The substrate is providedwith temperature measurement means including an infrared thermometer formeasuring a body surface temperature Tsk of the body surface and asubstrate thermometer for measuring a substrate temperature Tsub of thesubstrate, and the temperature measurement means measures the bodysurface temperature Tsk and the substrate temperature Tsub in the sameplace at least twice, that is, at a first timing A and a second timingB.

According to a sixth aspect of the second invention, an in vivo thermalresistance Rthbody is calculated from an equation Rthair×b/(a−b) when adifference between the body surface temperatures Tsk measured at thefirst timing A and measured at the second timing B is a, a differencebetween the substrate temperatures Tsub measured at the first timing Aand measured at the second timing B is b, and a thermal resistance ofthe air layer is Rthair.

According to a seventh aspect of the second invention, when a thermalresistance of the air layer is Rthair and a heat flow that flowssubstantially perpendicular to the body surface is Ith, the heat flowIth is obtained from an equation (Tsk−Tsub)/Rthair, and a predetermineddelay time is added to the substrate temperature Tsub in order tocorrect a response delay of the body surface temperature Tsk as comparedwith the substrate temperature Tsub.

According to an eighth aspect of the second invention, the deep bodytemperature TcoreA at the first timing A is compared with the deep bodytemperature TcoreB at the second timing B, both of which are calculatedbased on a heat flow IthA measured at the first timing A after thebiological data measurement device is wore on the body surface, a heatflow IthB measured at the second timing B after a predetermined time haselapsed from the first timing A, and a temporary value set in advance asthe in vivo thermal resistance Rthbody. A value of the in vivo thermalresistance Rthbody is corrected so that an absolute value obtained bysubtracting the deep body temperature TcoreB from the deep bodytemperature TcoreA falls within a predetermined determination valuerange.

According to a ninth aspect of the second invention, a ZHF state istemporarily created by raising a case temperature Tcase of a case, inwhich the biological data measurement device is accommodated, up to adeep body temperature Tcore using a heating element, thereby calculatingthe in vivo thermal resistance Rthbody based on the ZHF state.

According to a tenth aspect of the second invention, the case isprovided with calibration means for subjecting to a calibration by theheating element.

According to an eleventh aspect of the second invention, the biologicaldata measurement device includes a step of instructing to remove theheating element from the case when the case temperature Tcase exceeds apredetermined temperature Tth.

According to a twelfth aspect of the second invention, a step ofobtaining the in vivo thermal resistance Rthbody is executed when anenvironmental temperature changes at a rate at which the deep bodytemperature Tcore does not significantly change.

According to a thirteenth aspect of the second invention, a step ofobtaining the in vivo thermal resistance Rthbody is executed when aheart rate of the living organism as the measuring object is equal to orless than a predetermined threshold value.

According to a fourteenth aspect of the second invention, a step ofobtaining the in vivo thermal resistance Rthbody is executed when atemporary in vivo thermal resistance Rthbody is obtained by multiplyingan in vivo body core distance body_d from a body core to a body surfaceby a thermal resistivity from the body core to the body surface.

According to a fifteenth aspect of the second invention, the in vivothermal resistance Rthbody is calculated back from the substratetemperature Tsub and the body surface temperature Tsk, both of which areobtained at an initial stage of the measurement, so that the deep bodytemperature Tcore becomes a body temperature at rest which is input inadvance.

According to a sixteenth aspect of the second invention, an ECGmeasurement circuit for measuring electrocardiogram is mounted on thesubstrate. A wearing belt for wearing a case of the biological datameasurement device on the body surface is provided. At least twoelectrodes in contact with the body surface are disposed at apredetermined distance apart on the wearing belt. A contact portion isprovided between the wearing belt and the case in order to connect thetwo electrodes to the ECG measurement circuit. A body temperature signalmeasurement by the temperature measurement means is carried outsimultaneously with an electrocardiographic signal measurement by theECG measurement circuit.

In a biological data measurement device according to a seventeenthaspect of the second invention, a living organism having a first thermalresistance Rth1 from a core to a surface is a measuring object. Thebiological data measurement device includes a heat insulating layerwhich is disposed on a surface of the measuring object and has a secondthermal resistance Rth2; measurement means for measuring a first and asecond temperatures, which is segregated by the heat insulating layer;and adding means for adding a predetermined delay time to the secondtemperature in order to correct a response delay of the firsttemperature as compared with the second temperature. The firsttemperature is a bottom side temperature of a bottom surface of the heatinsulating layer, which is in contact with the body surface, and thesecond temperature is a top side temperature of a top surface of theheat insulating layer.

According to the first invention, the infrared thermometer and thesubstrate thermometer are provided on the substrate disposed at aposition spaced the predetermined distance from the body surface via thesupport member (heat insulating material), thus it is possible to easilymanufacture the biological data measurement device with a low cost.Moreover, since the heat insulating layer between the substrate and thebody surface is the air layer, the thermal resistance between thesubstrate and the body surface can be increased.

The heat insulating material serving as the support member forms thespace between the infrared thermometer and the body surface, thus erroron the ambient temperature can be reduced.

Since the biological data measurement device includes the transmitterwhich wirelessly transmits a body surface temperature measured by theinfrared thermometer and a substrate temperature measured by thesubstrate thermometer, the heat transfer through the wiring of the wiredtransmitter does not occur, and thus the deep body temperature can bemeasured with higher accuracy.

The first thermometer and the second thermometer are disposed inparallel on the substrate. The first thermometer includes a firstinfrared thermometer for measuring a body surface temperature of thebody surface and a first substrate thermometer for measuring a substratetemperature of the substrate. The second thermometer includes a secondinfrared thermometer for measuring a body surface temperature of thebody surface and a second substrate thermometer for measuring asubstrate temperature of the substrate. The upper surface of thesubstrate, on which the first thermometer is disposed, is covered withthe heat insulating material. Therefore, the deep body temperature canbe measured without measuring the in vivo thermal resistance by anothermethod.

According to the second invention, when a difference between the firsttemperatures measured at the first timing A and measured at the secondtiming B is a, a difference between the second temperatures measured atthe first timing A and measured at the second timing B is b, and thesecond thermal resistance is Rth2 (already known), the first thermalresistance (in vivo thermal resistance of the measuring object) Rth1 canbe calculated from the equation Rth2×b/(a−b). Therefore, the SHF methodis adopted as having a single temperature measurement unit, and the deepbody temperature can be obtained without measuring the in vivo thermalresistance of the measuring object by another unit.

As described above, two heat flows are measured in the same place at thetiming A and the timing B, which are temporally away from each other,using the same thermometer. Consequently, it is hardly influenced byvariation due to place or thermometer. Furthermore, the biological datameasurement device can be downsized with the significantly reduced powerconsumption, as compared with those employing the DHF or ZHF method.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1(a) shows a schematic plan view and FIG. 1(b) shows a schematiccross-sectional view thereof, both illustrating a basic aspect (firstembodiment) of the present invention.

FIG. 2(a) shows a schematic plan view and FIG. 2(b) shows across-sectional view thereof, both illustrating a second embodiment ofthe present invention.

FIG. 3(a) shows a schematic plan view and FIG. 3(b) shows across-sectional view thereof, both illustrating a third embodiment ofthe present invention.

FIG. 4(a) shows a schematic plan view and FIG. 4(b) shows across-sectional view thereof, both illustrating a fourth embodiment ofthe present invention.

FIG. 5(a) shows a schematic plan view and FIG. 5(b) shows across-sectional view thereof, both illustrating a fifth embodiment ofthe present invention.

FIG. 6(a) shows a schematic plan view and FIG. 6(b) shows across-sectional view thereof, both illustrating a sixth embodiment ofthe present invention, and FIG. 6(c) shows a cross-sectional viewillustrating a modified example of the fifth embodiment.

FIG. 7(a) shows a schematic view and FIG. 7(b) shows a cross-sectionalview of a main part, both illustrating a state where a biological datameasurement device according to the present invention is attached to theliving organism using a wearing belt.

FIG. 8(a) shows a schematic plan view and FIG. 8(b) shows across-sectional view thereof, both illustrating a seventh embodiment ofthe present invention.

FIG. 9 is a schematic cross-sectional view illustrating an eighthembodiment of the present invention.

FIG. 10(a) shows a graph illustrating a temperature gradient from a bodycore to an environmental temperature in the winter, and FIG. 10(b) showsa table illustrating a thermal resistivity, a thickness and a thermalresistance of each case in the wither, in the first to fourthembodiments of the present invention.

FIG. 11(a) shows a graph illustrating a temperature gradient from a bodycore to an environmental temperature in the summer, and FIG. 11(b) showsa table illustrating a thermal resistivity, a thickness and a thermalresistance of each case in the summer, in the first to fourthembodiments of the present invention.

FIG. 12(a) shows a graph illustrating a temperature gradient from a bodycore to an environmental temperature, which is measured by a firstthermometer and a second thermometer, and FIG. 12(b) shows a tableillustrating a thermal resistivity, a thickness and a thermal resistanceof each case at that time, in the fifth embodiment of the presentinvention.

FIG. 13(a) shows a schematic cross-sectional view illustrating abiological data measurement device attached onto the body surface via awearing belt, and FIG. 13(b) shows a plan view of the biological datameasurement device, in a ninth embodiment of the present invention.

FIG. 14(a) is a schematic view illustrating a circuit system installedon a substrate of the biological data measurement device according tothe ninth embodiment, and an exemplified arrangement of electrodes (two)provided on the wearing belt.

FIG. 14(b) is a schematic view illustrating another exemplifiedarrangement of electrodes (four) provided on the wearing belt, in theninth embodiment.

FIG. 15(a) shows a graph illustrating time constant correction of thedetected body surface temperature and the substrate temperature, andFIG. 15(b) shows a flowchart illustrating a step of executing the timeconstant correction, in a tenth embodiment of the present invention.

FIG. 16(a) is a graph illustrating a method for obtaining an in vivothermal resistance Rthbody from a transient response at the time ofwearing as an eleventh embodiment of the present invention.

FIG. 16(b) is a flowchart illustrating steps of increasing anddecreasing the in vivo thermal resistance Rthbody by the method.

FIG. 16(c) is a graph illustrating a method for directly obtaining thein vivo thermal resistance based on the body surface temperature and thesubstrate temperature as another method of the eleventh embodiment.

FIG. 16(d) is a flowchart illustrating operations according to anothermethod of the eleventh embodiment.

FIG. 17(a) shows a graph illustrating a method for obtaining an in vivothermal resistance Rthbody using a heating element, FIG. 17(b) shows aflowchart illustrating steps of increasing and decreasing the in vivothermal resistance Rthbody by the method, as a twelfth embodiment of thepresent invention.

FIG. 18(a) shows a graph illustrating a method for obtaining an in vivothermal resistance Rthbody using a heating element, FIG. 18(b) shows aflowchart illustrating steps of increasing and decreasing the in vivothermal resistance Rthbody by the method, as a thirteenth embodiment ofthe present invention.

FIG. 19(a) is a flowchart illustrating a method for requesting to a userto input a distance (body_d) from a body core to epidermis, as afourteenth embodiment of the present invention.

FIG. 19(b) is a flowchart illustrating a method for detecting a posturefrom acceleration to correct a body surface temperature and a substratetemperature, as a fifteenth embodiment of the present invention.

FIG. 20(a) shows a block diagram illustrating an ECG measurement circuitinstalled in the ninth embodiment, and FIG. 20(b) shows an explanatoryview illustrating operations of each part thereof, as a sixteenthembodiment of the present invention.

FIG. 21(a) shows a block diagram illustrating a GSR measurement circuitinstalled in the ninth embodiment, and FIG. 21(b) shows an explanatoryview illustrating operations of each part thereof, as a sixteenthembodiment of the present invention.

FIG. 22(a) shows a block diagram illustrating a GSR driving circuitinstalled in the ninth embodiment, and FIG. 22(b) shows an explanatoryview illustrating operations of each part thereof, as a sixteenthembodiment of the present invention.

FIG. 23(a) shows a schematic cross-sectional view illustrating an aspectin which a case of a biological data measurement device is disposed on awearing belt, and FIG. 23(b) shows a plan view of the case, as aseventeenth embodiment of the present invention.

FIG. 24 is a plan view of the wearing belt having four electrodes forattaching the case to a measuring target site as viewed from a measuringtarget site side.

FIG. 25(a) shows a schematic plan view illustrating an aspect in which acase of a biological data measurement device is connected to a wearingbelt with a detachable hook, FIG. 25(b) shows a cross-sectional viewthereof, and FIG. 25(c) an exemplified hook, as an eighteenth embodimentof the present invention.

FIG. 26(a) shows a plan view illustrating an aspect in which abiological data measurement device is installed on a single substrate,and FIG. 26(b) shows a cross-sectional view thereof, as a nineteenthembodiment of the present invention.

FIG. 27(a) shows a plan view illustrating an aspect in which abiological data measurement device is dividedly installed on twosubstrates, and FIG. 27(b) shows a cross-sectional view thereof, as atwentieth embodiment of the present invention.

FIG. 28(a) is a schematic cross-sectional view illustrating a firstexample of an electrical-mechanical contact portion between a wearingbelt and a case of a biological data measurement device.

FIG. 28(b) is a schematic cross-sectional view illustrating a secondexample of the electrical-mechanical contact portion between the wearingbelt and the case of the biological data measurement device.

FIG. 28(c) is a schematic cross-sectional view illustrating a thirdexample of the electrical-mechanical contact portion between the wearingbelt and the case of the biological data measurement device.

FIG. 28(d) is a schematic cross-sectional view illustrating a fourthexample of the electrical-mechanical contact portion between the wearingbelt and the case of the biological data measurement device.

FIG. 28(e) is a schematic cross-sectional view illustrating a fifthexample of the electrical-mechanical contact portion between the wearingbelt and the case of the biological data measurement device.

FIG. 29 is a schematic view introducing an SHF method as a first priorart.

FIG. 30 is a schematic view introducing a DHF method as a second priorart.

FIG. 31 is a schematic view introducing a ZHF method as a third priorart.

DESCRIPTION OF THE EMBODIMENTS

Some embodiment according to the present invention will be describedwith reference to FIGS. 1 to 28 . However, the present invention is notlimited to these embodiments.

First, referring to FIG. 1 , a biological data measurement device 1 ofthe present invention includes a substrate 10 provided with athermometer (temperature measurement means) 20 as a basic form (firstembodiment). The substrate 10 is disposed at a position spaced apredetermined distance from a body surface BS of a living organism as ameasuring object via a support member (described later) (for example, ata position spaced about 3 mm from the body surface BS).

The substrate 10 is, for example, a polyimide substrate. It ispreferable to set a thickness of the substrate 10 to about severalhundred microns to reduce the heat capacity. It is also preferable thatthe substrate 10 is in a shape of a square of 30 mm² or more. However,the substrate 10 may be a circle or a polygon other than a square,having substantially the same area.

Although not shown in detail, the thermometer 20, corresponding to thetemperature measurement means, includes an infrared thermometer 21 formeasuring a temperature Tsk of the body surface BS, and a substratethermometer 22 for measuring a substrate temperature Tsub of thesubstrate 10. The infrared thermometer 21 is disposed on a lower surfaceside of the substrate 10 so as to face the body surface BS. A hole maybe formed in the substrate 10, and the infrared thermometer 21 may bemounted in the hole.

A bolometer detector, a thermopile detector or the like is used as theinfrared thermometer 21 to measure an amount of infrared radiation ofthe body surface BS. The substrate thermometer 22 is a thermometer formeasuring the substrate temperature Tsub of the substrate 10. Thesubstrate thermometer 22 may be provided separately from the infraredthermometer 21; however, a calibration thermometer equipped with theinfrared thermometer 21 may be used as the substrate thermometer 22.

When a thermal resistance of an air layer A between the substrate 10 andthe body surface BS is Rthair, a heat flow (heat flux) Ith that flowssubstantially perpendicular to the body surface BS can be obtained fromthe equation (Tsk−Tsub)/Rthair.

A thermal resistance Rth between the substrate 10 and body surface BScan be increased by forming the air layer A. However, a solid heatinsulating layer made of, for example, a foam material or the like maybe adopted instead of the air layer A. In this case, a thermometer formeasuring the body surface temperature is provided on surface on a bodysurface side of the solid heat insulating layer, instead of the infraredthermometer.

When a deep body temperature of the living organism is Tcore, and athermal resistance from a deep tissue to the body surface BS in theliving organism is Rthbody, the deep body temperature Tcore can beobtained from the equation Tsk+Ith×Rthbody.

In the first embodiment, the in vivo thermal resistance Rthbody ismeasured by another method (not shown). As one example of anothermethod, the in vivo thermal resistance Rthbody is measured from an invivo electrical resistivity measured by in vivo electrical resistivitymeasurement means, which measures the in vivo electrical resistivity(Galvanic skin resistance, GSR) by flowing a weak electric current (forexample, about 0.2·A) to the living organism with a pair of electrodes.The present invention also encompasses an embodiment including the invivo electrical resistivity measurement means.

Referring to FIG. 2 , the biological data measurement device 1 accordingto a second embodiment is provided with a support member 30 thatsupports the substrate 10 at a predetermined height position on the bodysurface BS. The support member 30 preferably employs a heat insulatingmaterial 31, e.g. a foamed plastic material or the like, which has thethermal resistance Rth as large as possible, and is hardly deformed byexternal force.

Examples of the foamed plastic material include polyurethane,polystyrene, and the like. Rigid urethane foam made of polyurethane hasa thermal resistivity equivalent to 40 m·K/W at the stationaryatmosphere. A compressive strength of several hundred gf/cm² to 1kgf/cm² can be produced.

In this embodiment, the support member 30 (heat insulating material 31)forms a substantially sealed space as the air layer A between theinfrared thermometer 21 and the body surface BS when attaching onto thebody surface BS, and covers the substrate surface including an uppersurface, other than the air layer.

In a third embodiment shown in FIG. 3 , the biological data measurementdevice 1 is provided with a case 40 for reducing the lateral release ofa heat flow Ith from the body surface BS. The case 40 includes a boxbody of which a bottom surface (surface on a body surface BS side) isopen, and which has a top plate 401 and a side plate 402 bent downwardat a substantially right angle from a peripheral edge of the top plate401. The substrate 10 is accommodated in the case 40 while beingsupported by the heat insulating material 31.

On the other hand, in the third embodiment, the substrate 10 is providedwith a transmitter 24 and a calculator 25. The calculator 25 calculatesthe heat flow Ith from the body surface temperature Tsk measured by theinfrared thermometer 21, the substrate temperature Tsub measured by thesubstrate thermometer 22, and the thermal resistance Rthair of the airlayer A, as described above as one example. The transmitter 24wirelessly transmits the calculated values to a data collection/analysisdevice as a parent device (not shown).

A wireless module or the like is used as the transmitter 24, and amicrocomputer or the like is used as the calculator 25. In a case wherethese modules or packages include a heat generation component, of whichheat (in many cases, minute heat) causes faults in the measurement ofthe deep body measurement, the transmitter 24 and/or the calculator 25can be disposed outside the case 40 as one of countermeasures.

As another method, a high thermal conductive material for improving theheat conduction of the body surface BS with the transmitter 24 and/orthe calculator 25 may be provided on the air layer A (for example, alower surface of the substrate 10) to release the heat generated by thetransmitter 24 and/or the calculator 25 to the body surface BS.

Furthermore, the transmitter 24 and/or the calculator 25 may be providedon an upper surface of the substrate 10 to release the heat to theatmosphere, or a heat insulator may be interposed between thetransmitter 24 and/or the calculator 25 and the thermometer 20.

As another aspect, the calculator 25 may be provided on the parentdevice (data collection/analysis device) side, and the transmitter 24may transmit data including the body surface temperature Tsk and thesubstrate temperature Tsub to the parent device, thereby obtaining theheat flow Ith and the deep body temperature Tcore on the parent deviceside. This aspect is also encompassed in the present invention.

It is preferable that the case 40 is made of a material that reduces thetemperature distribution in a horizontal direction and is transmissiveto the radio wave (electromagnetic wave) of the transmitter 24. Anexemplified material is alumina. In addition, the thermal resistivity ofalumina is 0.03 m·K/W.

A patterned printed circuit board can also be used instead of alumina.In this case, a conductor (copper foil) is excluded from a specificportion 40 a (an upper right corner in FIG. 3(a)) of the transmitter 24,corresponding to a communication antenna so that the radio wave canpass. The side plate 402 of the case 40 may be made of metal.

The transmitter 24 can use a radio band of 2.4 GHz or 13.56 MHz(industrial, scientific and medical radio bands). Although not shown,the substrate 10 is provided with a battery (preferably a secondarybattery) for supplying power to the transmitter 24 and/or the calculator25. However, the power may be supplied from the parent device side at13.56 MHz.

In a fourth embodiment shown in FIG. 4 , cylindrical heat insulatingmaterials 311, 312 are used as the support member 30. The heatinsulating materials 311, 312 are arranged concentrically. The heatinsulating material 311 is on the inside and the heat insulatingmaterial 312 is on the outside.

In the fourth embodiment, the inner heat insulating material 311 isprovided with a cylindrical lower heat insulating material 311 aprovided on the lower surface side of the substrate 10 to form a sealedspace (air layer A) between the infrared thermometer 21 and the bodysurface BS when attaching onto the body surface BS, and an upper heatinsulating material 311 b disposed between the upper surface of thesubstrate 10 and an inner surface of the case 40.

The outer heat insulating material 312 is a support member forsupporting an outer peripheral side of the substrate 10, and is providedwith a cylindrical lower heat insulating material 312 a provided on thelower surface side of the substrate 10 and an upper heat insulatingmaterial 312 b disposed between the upper surface of the substrate 10and the inner surface of the case 40.

Moreover, in the fourth embodiment, the upper heat insulating material311 b and the lower heat insulating material 311 a, included in theinner heat insulating material 311, have the same diameter, but may havedifferent diameters. Similarly, the upper heat insulating material 312 band the lower heat insulating material 312 a, included in the outer heatinsulating material 312, have the same diameter, but may have differentdiameters.

In the fourth embodiment, the heat insulating materials 311, 312 arecylindrical, but may be square tubular. Generally, the heat insulatingmaterial loses the thermal resistivity as the compressive strengthincreases, so that the heat resistivity can be increased by adopting thecylindrical heat insulating material. For example, polystyrol has athermal resistivity of 8 m·K/W. That is, polystyrol has a sufficientstrength but a low thermal resistivity, thus it can be partially used.

Referring to FIG. 5 , the biological data measurement device 1 accordingto a fifth embodiment is provided with two thermometers, i.e. a firstthermometer 20 a and a second thermometer 20 b. Both of the thermometers20 a, 20 b include the infrared thermometer 21 and the substratethermometer 22.

Two substrates 10 a, 10 b are used as the substrate 10 on which the twothermometers 20 a, 20 b are installed. The first thermometer 20 a isprovided on one substrate 10 a, and the second thermometer 20 b isprovided on the other substrate 10 b. In this embodiment, both of thetransmitter 24 and the calculator 25 are disposed on a side of thesubstrate 10 a.

The substrate 10 a and the substrate 10 b are connected by a flexiblesubstrate 11. The second thermometer 20 b is connected to thetransmitter 24 and/or the calculator 25 via a wiring in the flexiblesubstrate 11. As another aspect, the thermometers 20 a, 20 b may bejuxtaposed on the same substrate 10.

A difference between the thermometers 20 a, 20 b is that, as shown inFIG. 5(b), a heat insulating material 313 is disposed above one of thethermometers, i.e. the first thermometer 20 a, and a space is formedabove a side of the second thermometer 20 b.

The calculator 25 obtains the deep body temperature Tcore of the livingorganism based on the body surface temperature Tsk and the substratetemperature Tsub, measured by the thermometers 20 a, 20 b, as follows.

That is, when a body surface temperature measured by the firstthermometer 20 a is Tsk1, a heat flow that flows substantiallyperpendicular to the body surface BS at a portion of the firstthermometer 20 a is Ith1, a body surface temperature measured by thesecond thermometer 20 b is Tsk2, a heat flow that flows substantiallyperpendicular to the body surface BS at a portion of the secondthermometer 20 b is Ith2, and the in vivo thermal resistance from thedeep tissue to the body surface BS in the living organism is Rthbody,the calculator 25 calculates Rthbody from the equation(Tsk2−Tsk1)/(Ith1−Ith2), and then obtains the deep body temperatureTcore of the living organism from the equation (Ith1×Rthbody+Tsk1) or(Ith2×Rthbody+Tsk2).

Additionally, when a substrate temperature measured by the substratethermometer 22 of the first thermometer 20 a is Tsub1, a substratetemperature measured by the substrate thermometer 22 of the secondthermometer 20 b is Tsub2, and the thermal resistance of the air layer Ais Rthair, the heat flow Ith1 is obtained from the equation(Tsk1−Tsub1)/Rthair, and heat flow Ith2 is obtained from the equation(Tsk2−Tsub2)/Rthair, as described above.

As described above, according to the fifth embodiment, the in vivothermal resistance Rthbody from the deep tissue to the body surface BSin the living organism is calculated, thus it is not necessary tomeasure (estimate) the in vivo thermal resistance Rthbody by anothermeasurement means (for example, the in vivo electrical resistancemeasurement means, as stated above).

Referring to FIGS. 6(a) and 6(b), the biological data measurement device1 according to a sixth embodiment is implemented on the basis of, forexample, the fourth embodiment shown in FIG. 4 , with improvedwearability for the living organism.

That is, in the sixth embodiment, an entire lower surface (a surfacefacing the body surface BS) of the case 40 is covered with a sheet 51,and a lower surface (a surface facing the body surface BS) of the sheet51 is coated with an adhesive gel 52 with a predetermined thickness, asshown in FIG. 6(b). Accordingly, the biological data measurement device1 can be smoothly attached onto the body surface BS.

A (highly elastic) material harder than the adhesive gel 52 is used forthe sheet 51 in order to prevent the soft adhesive gel 52 from beingdeformed so that a thickness of the air layer A does not change.

In this case, the infrared thermometer 21 measure a temperature of thesheet 51. The thermal resistance Rth of each of the sheet 51 and theadhesive gel 52 may be subtracted to obtain the in vivo thermalresistance Rthbody. As another method, the body surface temperature Tskcan be measured using an infrared transmissive material in the sheet 51and the adhesive gel 52.

The thermal resistivity can be increased by enclosing a rare gas such asxenon, kyrton, argon or the like in the space serving as the air layerA. Furthermore, sweat discharge grooves may be formed in the adhesivegel 52 by, for example, subjecting the sheet 51 to the embossingprocess. Consequently, this embodiment has an advantageous effect ofmaintaining tackiness of the adhesive gel.

As a modified example of the sixth embodiment, the sheet 51 and theadhesive gel 52 may be removed from a center portion of a bottom surfaceof the case 40, as shown in FIG. 6(c), in order to allow the infraredthermometer 21 to directly measure the body surface temperature. Thepresent invention also encompasses this aspect. A configuration of thesixth embodiment is also applicable to the fifth embodiment illustratedin FIG. 5 .

The biological data measurement device 1 is attached to a predeterminedregion (for example, chest, abdomen, etc.) of a living organism H via awearing belt 60, as shown in FIGS. 7(a) and 7(b). Furthermore, thebiological data measurement device 1 shown in FIG. 7(b) is thebiological data measurement device 1 according to the third embodimentillustrated in FIG. 3 , but may be the biological data measurementdevice 1 of another embodiment.

It is preferable that the wearing belt 60 has an elastic structure, andis made of a rubber material having a high elongation rate (preferably arubber material having an elongation rate of serval tens to hundreds %).The wearing belt 60 must not hinder the air permeability to the livingorganism H, and thus the wearing belt 60 may be a mesh structure for theimproved air permeability, as a prevention of heat stroke in the summer.

On the other hand, the case 40 has a low thermal resistance, thus thefaults may occur in the measurement of the body temperature due to rapidtemperature change when the case 40 is in contact with, for example, anarm, upon attaching to the living organism H. Therefore, in a seventhembodiment shown in FIG. 8 , a protective cover 70 for covering the case40 is provided.

The protective cover 70 is made of a heat insulating material thathardly transmits heat, for example, a highly foamable polyurethane orpolystyrene. The protective cover 70 is formed as a box of which abottom surface larger than the case 40 is open, and is provided withwearing belt insertion openings 71, 71 on opposite side surfaces,through which the wearing belt 60 passes.

An eighth embodiment will be described with reference to FIG. 9 . In theeighth embodiment, a case is needed to prevent that the body surfaces BSraises by the fastening force of the wearing belt 60 and a clearance ofthe air layer A (a distance between the substrate 10 and the bodysurface BS) changes when the biological data measurement device 1 isattached onto the body surface BS using the wearing belt 60, as statedabove. A case 40A is used as such a case, which includes a case body 41of which a top surface is open and a lid 42 that detachably covers thetop surface of the case body 41.

The case body 41 is a box body of which the top surface is open, andwhich has a square bottom plate 411 and side plates 412 standing on foursides thereof. The substrate 10, provided with the thermometer 20, thetransmitter 24, the calculator 25 and the like, is accommodated in thecase body 41 while being supported by the heat insulating material 31 asthe support member 30. The top surface of the case body 41 is closedwith the lid 42 upon using.

In this embodiment, both of the case body 41 and the lid 42 are made ofacrylic resin, but other synthetic resin materials may be used as longas they are materials with low thermal resistance and low heat capacityand transmissive to the infrared rays. Moreover, the lid 42 does notneed to be a material transmissive to the infrared ray, but needs to bea material transmissive to the radio wave (electromagnetic wave) of thetransmitter 24.

The clearance of the air layer A formed between the substrate 10 and thebody surface BS is kept to be constant by using such as case 40A even ifthe biological data measurement device 1 is strongly fastened to thebody surface BS with the wearing belt 60.

The biological date measurement device 1 according to the eighthembodiment is provided with a high thermal conductive film 53 fortransmitting to the substrate 10 the heat entering into and leaving froma side surface (side plate 412) of the case 40A. The term “high thermalconductive” is defined as having a thermal resistivity of about 0.01m·K/W (thermal conductivity of about 100 W/m/K). An aluminum foil ispreferably used for the high thermal conductive film 53.

According to this embodiment, the high thermal conductive film (aluminumfoil) 53 is disposed so as to be in close contact with respectivesurfaces from lower peripheral edges of the substrate 10 to an innersurface of the heat insulating material 31. Consequently, the bodysurface temperature (skin temperature) Tsk varies via the substrate 10even when the environmental temperature changes, thus it is possible toeliminate errors caused by the solely changed body surface temperatureTsk.

It is preferable that the high thermal conductive film 53 has aninfrared emissivity close to zero (substantially 0), for the temperaturechange of the heat insulating material 31 is not radiated toward the airlayer A even when the heat cannot be sufficiently transferred to thesubstrate 10 due to the limited heat conduction.

The high thermal conductive film 53 is applicable to other embodimentsincluding the case 40 of which the bottom surface is open, asillustrated in FIGS. 3 to 6 . In this case, the high thermal conductivefilm 53 is arranged from the side plate 402 to the substrate 10 withinthe case 40, for example, as shown in FIG. 5(b).

A correlation between the thermal resistance and the temperature in eachcase when measuring the body temperature will be described withreference to the biological data measurement device 1 according to thefourth embodiment illustrated in FIG. 4 .

A graph shown in FIG. 10(a) indicates a transition of the heat flow(heat flux) in each case in the winter, where a horizontal axis denotesthe thermal resistance Rth (K·m²/W) and a vertical axis denotes thetemperature (·C). This graph is drawn assuming that it is the winterseason where, for example, the deep body temperature is 36.5·C, theenvironmental temperature is 0·C, and the user wears underwear, shirtsand sweater.

See a table shown in FIG. 10(b) for data on thermal resistivity andthermal of each case, including: a region from the body core to the bodysurface (assuming that the depth is 25 mm), stationary atmosphere(assuming that 3-mm air layers are formed above and below the substrate,respectively), winter clothing (assuming that 1-mm air layers are formedunder the underwear, the shirts and the sweater, respectively), and openatmosphere (with convention).

In the graph of FIG. 10(a), a gradient (T/Rth) of the straight line isthe heat flow (heat flux) Ith, and Ith is 55 W/m² in this example.

A graph shown in FIG. 11(a) indicates a transition of the heat flow(heat flux) in each case in the summer, where a horizontal axis denotesthe thermal resistance Rth (K·m²/W) and a vertical axis denotes thetemperature (·C). This graph is drawn assuming that it is the summerseason where, for example, the deep body temperature is 36.5·C, theenvironmental temperature is 25·C, and the user wears shirts only.

See a table shown in FIG. 11(b) for data on thermal resistivity andthermal of each case, including: a region from the body core to the bodysurface (assuming that the depth is 25 mm), stationary atmosphere(assuming that 3-mm air layers are formed above and below the substrate,respectively), summer clothing (assuming that 1-mm air layer is formedunder the shirts), and open atmosphere (with convention).

In the graph of FIG. 10(b), a gradient (T/Rth) of the straight line isthe heat flow (heat flux) Ith, and Ith is 23 W/m² in this example.

A correlation between the thermal resistance and the temperature in eachcase for the biological data measurement device 1 with the twothermometers, according to the fifth embodiment of FIG. 5 , whenmeasuring the body temperature will be described with reference to FIG.12 .

A graph shown in FIG. 12(a) is drawn assuming that it is the summerseason, where the deep body temperature is 36.5·C, the environmentaltemperature is 25·C, and the user wears shirts only, as in the graph ofFIG. 11(a).

See a table shown in FIG. 11(b) for data on thermal resistivity andthermal of each case, including: a region from the body core to the bodysurface (assuming that the depth is 25 mm), stationary atmosphere(assuming that 3-mm air layers are formed above and below the substrateof the second thermometer 20 b, respectively), heat insulating material(assuming that polystyrene having a thickness of 3 mm is provided on theupper surface of the substrate of the first thermometer 20 a), summerclothing (assuming that 1-mm air layer is formed under the shirts), andopen atmosphere (with convention).

In the graph of FIG. 12(a), a broken line denotes the heat flow Ith1measured by the first thermometer 20 a, and a solid line denotes theheat flow Ith2 measured by the second thermometer 20 b. Since the heatflow Ith1 is different from the heat flow Ith2, the deep bodytemperature Tcore can be calculated based on the body surfacetemperature Tsk, the heat flow Ith1 and the heat flow Ith2.

As described above, the biological data measurement device of thepresent invention is configured to include the substrate, the infraredthermometer and the substrate thermometer, both of which are installedon the substrate, and the support member for supporting the substrate ata position spaced the predetermined distance from the body surface as abasic configuration. Thus, a simple configuration can be implementedwith a low cost. Moreover, since the heat insulating layer between thesubstrate and the body surface is the air layer, the thermal resistancebetween the substrate and the body surface can be increased.

The biological data measurement device 1 according to a ninth embodimentwill be described with reference to FIGS. 13(a), 13(b), 14(a) and 14(b).The biological data measurement device 1 is provided with a case 100attached onto the body surface, such as chest, abdomen or the like,using a wearing belt 200.

The case 100 is made of a box body including a bottom plate, side platesand an upper lid. The substrate 10 is supported via the support member30 made of the heat insulating material 31 in the case 100, therebyforming a predetermined space A between the bottom plate and thesubstrate 10. The thermometer 22, including the infrared thermometer 21and the substrate thermometer 22, is disposed on a bottom surface sideof the substrate 10, as in the embodiments stated above.

The case 100 basically adopts a configuration of the respectiveembodiments stated above, and an environmental thermometer 330 formeasuring an ambient temperature is additionally disposed on an outersurface of the upper lid of the case 100 in the ninth embodiment. Theenvironmental thermometer 330 does not need to have particularspecification, and may employ commercially available products.

The substrate 100 is further provided with various signal processingcircuit clusters 300. In the ninth embodiment, the signal processingcircuit cluster 300 includes an ECG (electrocardiogram) measurementcircuit 310, a GSR (galvanic skin resistance) measurement circuit 311′as in vivo electrical resistance measurement means for measuring anelectrical resistance of the skin (in vivo), a GSR driving circuit 312′,a communication circuit 313′, a control circuit 314, a memory circuit315, a power supply circuit 316 and a battery 317.

The communication circuit 313′ includes the transmitter 24 and performscommunication with the outside. The control circuit 314 employs amicrocomputer, CPU, MPU, etc., and controls each circuit. The memorycircuit 315 stores raw data, calculation results and the like. The powersupply circuit 316 converts the voltage of the battery 317 to apredetermined voltage and supplies the power to each circuit.

The wearing belt 200 is provided with two electrodes 211, 212, both ofwhich are in contact with the body surface. Contact potions C1, C2, bothof which connect the electrodes 211, 212 to each circuit, i.e. the ECGmeasurement circuit 310, the GSR measurement circuit 311′, and the GSRdriving circuit 312′, are provided between the wearing belt 200 and thecase 100.

The contact portion C1 includes a combination of a male contact 221connected to one electrode 211 via a wiring on a side of the wearingbelt 200, and a female contact 111 provided on the upper lid of the case100 as an engaging side of the male contact 221.

The contact portion C2 includes a combination of a male contact 222connected to the other electrode 212 via a wiring on a side of thewearing belt 200, and a female contact 112 provided on the upper lid ofthe case 100 as an engaging side of the male contact 222.

In this example, the ECG measurement circuit 310, the GSR measurementcircuit 311′ and the GSR driving circuit 312′ are connected to thefemale contacts 111, 112. The electrodes 211, 212 are simultaneouslyused in the ECG measurement and the GSR measurement.

It is preferable that a disk-shaped conductive magnet, similar to a coinor a button, is used in the male contacts 221, 222, and a dish-shapedmagnetic element is used in the female contacts 111, 112. However, theconductive magnet may be used in the male contact, the magnetic elementmay be used in the female contact, or alternatively, both male andfemale contacts may use the conductive magnets.

It should be noted that the terms “male” and “female” for the contactsare for easier understanding. It is unnecessary that the male contacthas to be a projection and the female contact has to be a recess. Themale contact can be referred as to a first contact, and the femalecontact as to a second contact.

As a modified example, two electrodes 213, 214 may be added outwardly ofthe electrodes 211, 212, as four electrodes in total, accompanying withadditional contact portions C3, C4, as shown in FIG. 14(b). The contactportions C3, C4 may have the same configuration as the contact portionsC1, C2.

In this case, the GSR driving circuit 312′ is connected to theadditional outer electrodes 213, 214 via the contact portions C3, C4,thereby supplying a drive current from the GSR driving circuit 312′ tothe electrodes 213, 214.

The ECG measurement circuit 310 and the GSR measurement circuit 311′ areconnected to the inner electrodes 211, 212 via the contact portions C1,C2, thereby measuring a GSR voltage while simultaneously measuring anECG signal with the electrodes 211, 212.

As described above, it is possible to eliminate influence of contactresistance between the electrode and the skin by dividing the fourelectrodes 211 to 214 into the electrodes 213, 214 on a drive currentsupplying side and the electrodes 211, 212, on a voltage measurementside, as a four-electrode (four-terminal) method. This mechanism isparticularly effective when a GSR absolute value is important. Anotheradvantageous effect is that an electrocardiogram (ECG) voltagemeasurement is hardly influenced by a noise caused by GSR driving.

As described above, in the ninth embodiment, the ECG measurement circuit310 is provided for measuring the electrocardiogram. Therefore, aphysiological state of the user can be confirmed with higher accuracy bysimultaneously measuring the electrocardiogram (ECG) with the deep bodytemperature Tcore obtained by a temperature measurement system includingthe thermometer 20.

That is, the deep body temperature Tcore responds late to exercise loadand/or environmental fluctuation. Meanwhile, heart rate obtained fromthe ECG responds immediately (sensitively) to the exercise load.Therefore, exercise status of the user, including start, continuation ortermination of the exercise, can be confirmed by adopting the ECGmeasurement together with the deep body temperature measurement.

It is possible to send a warning to the user him/herself or a supervisorof the user to cease the exercise when the deep body temperature Tcoreexceeds a predetermined threshold value. The environmental fluctuationcan be grasped the substrate temperature Tsub and other thermometers,and thus it is possible to issue environment alerts in the same way. Asdescribed above, since the environmental thermometer 330 is disposed onthe outer surface of the upper lid of the case 100, the measuredtemperature value of the environmental thermometer 330 can also bereflected to the deep body temperature Tcore.

It is preferable that an adhesive film 121 made of silicone or the likeis provided on the bottom surface of the case so that no gap is formedbetween the skin and the bottom plate of the case, and further the case100 is not shifted due to sweating, when the case 100 is attached ontothe body surface by the wearing belt 200.

A time constant correction of a tenth embodiment will be described withreference to FIGS. 15(a) and 15(b). The body surface temperature Tskoften temporally lags behind the substrate temperature Tsub due to thesubcutaneous thermal resistance and heat capacity. This is because thesubstrate temperature Tsub depends on the ambient temperature and theheat capacity of the substrate 10 is relatively small.

Calculation failures occur in the deep body temperature Tcore due to thetemporal delay of the body surface temperature Tsk, as indicated by abroken line of FIG. 15(a). The calculation errors of the deep bodytemperature Tcore can be reduced by adding a predetermined delay to thesubstrate temperature Tsub and eliminating a delay difference with thebody surface temperature Tsk.

A delay amount Tsub_d for the substrate temperature Tsub is created bycalculating the equation, for example,Tsub_d[n+1]=Tsub_d[n]+(Tsub[n+1]−Tsub_d[n])/·sub, using time series datasuch as Tsub[n−1], Tsub[n], Tsub[n+1] . . . , thereby obtaining thedelay amount Tsub_d for the substrate temperature Tsub.

As one example, a time constant of about 50 seconds can be added to thesubstrate temperature Tsub as a delay amount by setting·sub to about 50if the time series data exists every second.

Since there is a correlation between the in vivo thermal resistanceRthbody and·sub, it is possible to select·sub in response to a value ofthe in vivo thermal resistance Rthbody based on a correlation tableprepared in advance. Sometimes overshoot (refer to a broken line in FIG.15(a)) may appear when, for example, the user starts to wear thebiological data measurement device 1 onto the body surface. It is alsopossible to store a shape of the overshoot and remove it.

A method for obtaining the in vivo thermal resistance Rthbody from atransient response upon wearing will be described with reference toFIGS. 16(a) to 16(d), as an eleventh embodiment. According to thismethod, an absolute value of the deep body temperature can be obtainedusing the SHF (single-heat-flux) method.

After the user starts to wear the biological data measurement device 1,the heat flow Ith shifts from a large value to a small value. Referringto FIG. 16(a), the in vivo thermal resistance Rthbody, which is anunknown value, is obtained from two heat flows Ith at the timings A, Bduring the heat flows Ith shifts.

First, data is recorded before wearing in order to record the transientresponse at the time of wearing. An initial value of the in vivo thermalresistance Rthbody is set to a temporary value, but the overshootappears by setting the in vivo thermal resistance Rthbody to arelatively large value. A timing A is set as a first timing around atthe time when the overshoot appears. Consequently, it is possible toavoid an unstable period in an initial stage of wearing.

A timing B, as a second timing, is preferably set to a timing aboutseveral minutes, preferably about 5 to 10 minutes, after the timing A.If the elapsed time is shorter than about 5 to 10 minutes, the faultseasily occur since there is not enough time to change from the timing A.If the elapsed time is longer than about 5 to 10 minutes, the bodytemperature of the user may change, which is not preferable.

Referring also to the flowchart of FIG. 16(b), a deep body temperatureTcoreA at the timing A and a deep body temperature TcoreB at the timingB are calculated based on the temporarily set value of the in vivothermal resistance Rthbody, and then TcoreA is compared with TcoreB.

Accordingly, in a case where TcoreA is smaller than TcoreB, a value ofthe in vivo thermal resistance Rthbody is increased; on the other hand,in a case where TcoreA is larger than TcoreB, a value of the in vivothermal resistance Rthbody is decreased, thereby calculating the deepbody temperature Tcore again.

In a case where an absolute value of TcoreA−TcoreB, |TcoreA−TcoreB|, isequal to or falls below a determination value, a value at that time isadopted as a value of the in vivo thermal resistance Rthbody,increase/decrease in Rthbody is ceased and the deep body temperatureTcore is finally calculated.

Regarding increase/decrease the in vivo thermal resistance Rthbody, itis possible to use a binary search that sequentially halves a changeamount of increase/decrease. In a case where a solution cannot be found,it is possible to instruct the user to wear the device again; oralternatively, it is also possible to use the previously obtained value.The accuracy can be further improved by storing the in vivo thermalresistance Rthbody for each region, such as abdomen, back, etc., and byaveraging for each region.

It is also possible to determine a gradient of the deep body temperatureTcore from several points between sections A and B using a differentialwaveform of the deep body temperature Tcore between the sections A and Bafter the overshoot is eliminated, instead of comparison between TcoreAand TcoreB.

Referring to FIGS. 16(c) and 16(d), it is also possible to, furthermathematically, determine the in vivo thermal resistance Rthbodydirectly from gradients of the substrate temperature Tsub and the bodysurface temperature Tsk.

That is, a gradient of the substrate temperature Tsub obtained from adifference between the substrate temperature TsubA at the timing A andthe substrate temperature TsubB at the timing B is a, and a gradient ofthe body surface temperature Tsk obtained from a difference between thebody surface temperature TskA at the timing A and the body surfacetemperature TskB at the timing B is b. Then, it is only necessary tofind a state where a gradient of the deep body temperature Tcore iszero. As it is apparent from definitions of the in vivo thermalresistance Rthbody and the thermal resistance Rthair of the air layer,the gradient of the deep body temperature Tcore is zero whenRthbody/Rthair is b/(a−b).

The thermal resistance Rthair of the air layer A is already known, andthe gradients a, b of the substrate temperature Tsub and the bodysurface temperature Tsk are obtained from respective temperatures at thetimings A, B as described above. Therefore, the in vivo thermalresistance Rthbody can be directly obtained from the equationRthair×b/(a−b).

The gradients a, b of the substrate temperature Tsub and the bodysurface temperature Tsk can be respectively obtained by differentiating,and thus it is also possible to directly obtain a value ofRthbody/Rthair using differential values corresponding to the gradients.Since the thermal resistance Rthair of the air layer can be recognizedby calibration, the in vivo thermal resistance Rthbody, which isunknown, is obtained.

A method for obtaining a value of Rthbody so that the absolute value ofTcoreA-TcoreB falls within a predetermined determination value, asdescribed above, includes a method for directly obtaining Rthbodywithout such repetitive calculation.

According to the DHF method, the deep body temperature Tcore is obtainedusing two heat flows measured at spatially distant places. Whereas theinvention according to the eleventh embodiment adopts the SHF method,while the absolute value of the deep body temperature Tcore can beobtained from the heat flows measured in the same place but at thetimings A, B, which are temporally away from each other.

As described above, two heat flows are measured in the same place at thetiming A and the timing B, which are temporally away from each other,using the same thermometer. Consequently, it is hardly influenced byvariation due to place or thermometer. Furthermore, the biological datameasurement device can be downsized with the significantly reduced powerconsumption, as compared with those employing the DHF or ZHF method.

However, this method can be established provided that the deep bodytemperature Tcore has not changed, while the heat flow at the timing Ais needed to be different from the heat flow at the timing B.Furthermore, it is necessary to execute processes when the environmentaltemperature changes at a rate at which the deep body temperature Tcorecannot change yet.

The measuring object in the invention according to the eleventhembodiment is not limited to the living organism, but the invention maybe applied to a structure having a heat source at depths, for example,electronic or electric devices, air conditioners, cooking devices,machine facilities, transport devices, buildings, geological researchesand the like. In addition, when the device is attached to the livingorganism, It can be mounted on a part of clothing, shoes, hat, gloves,earpieces, eyeglasses, etc.

Therefore, in the present invention, an object having a first thermalresistance from a core to a surface is a measuring object. The presentinvention also encompasses a biological data measurement device which isprovided with a heat insulating layer which is disposed on a surface ofthe measuring object and has a second thermal resistance; measurementmeans for measuring a first and a second temperatures, which issegregated by the heat insulating layer; calculation means forcalculating the first thermal resistance based on the first and thesecond temperatures measured at a first timing A, and the first and thesecond temperatures measured at a second timing B after a predeterminedtime has elapsed from the first timing A; and calculation means forcalculating a deep body temperature of the measuring object based on thefirst and the second thermal resistances, and the first and the secondtemperatures.

In a case where the measuring object is the living organism, the firstthermal resistance corresponds to the in vivo thermal resistanceRthbody, the heat insulating layer having the second thermal resistancecorresponds to the air layer having the air thermal resistance Rthair,and the first and second temperatures respectively correspond to thebody surface temperature Tsk and the substrate temperature Tsub.

A method for obtaining the in vivo thermal resistance Rthbody using aheating element, such as a heater, will be described with reference toFIGS. 17(a) and 17(b) as a twelfth embodiment.

In this embodiment, a ZHF (zero-heat-flux) state is temporarily createdby raising a case temperature to the deep body temperature Tcore,thereby calculating the in vivo thermal resistance Rthbody based on theZHF state.

When the substrate temperature Tsub and the body surface temperature Tskcoincide with the deep body temperature Tcore, the heat flow Ith doesnot flow (ZHF state). The ZHF state can be confirmed when substratetemperature Tsub and the body surface temperature Tsk become the sametemperature. The in vivo thermal resistance Rthbody is calculated backso that the coincident temperature is an answer for the calculation ofthe deep body calculation Tcore immediately before or after Tsub and Tskcoincide with Tcore.

In particular, the case temperature Tcase rises by placing a heatingelement, such as a heater or a hot pack, on the case 100 (refer to FIG.13 ). Hands or arms may be placed on the case 100 as the heatingelement. It is preferable to notify the user beforehand so thatcalibration using the heating element shall be done at rest since themeasurement failures occur if the true deep body temperature of the userfluctuates during the calibration.

It is preferable that, for example, a accept button for the calibrationusing the heating element is provided at any position of the case 100 toreceive the instruction from the user. A concept of the calibrationreception encompasses that a system automatically drives the heatingelement provided in the case 100 to carry out the calibration withoutthe instruction from the user. The user may be instructed to place theheating element on the case if needed.

The case temperature Tcase increases by the heating element (from timingA to timing B, in FIG. 17(a)). When the case temperature Tcase exceeds apredetermined temperature Tth by the heating, the user is instructed toremove the heating element from the case 100. Or alternatively, theheating may be automatically ceased. Instead of the case temperatureTcase, for example, the substrate temperature Tsub or the body surfacetemperature Tsk may be employed.

As in the eleventh embodiment, calculation and determination of the deepbody temperatures TcoreA, TcoreB at the timings A, B are repeated toobtain the optimal in vivo thermal resistance Rthbody. It is alsopossible to use data on the timings B, C both at which the temperaturedecreases.

Furthermore, upward or downward projection shapes of the deep bodytemperature Tcore may be determined using all measurement points fromthe timing A to the timing C in various ways (for example, using thedifferential waveform of Tcore, etc.). As another aspect, a coolingelement may be used instead of the heating element.

A method for obtaining the in vivo thermal resistance Rthbody fromfluctuation in the environmental temperature will be described withreference to FIGS. 18(a) and 18(b) as a thirteenth embodiment.

The inventors have confirmed from experiments that quite lots ofdiscontinuous points appear in the calculated value of the deep bodytemperature Tcore when a value of the in vivo thermal resistance Rthbodyis deviated, upon normally using. This is because, as long as the invivo thermal resistance Rthbody is deviated, the calculated value of thedeep body temperature Tcore fluctuates even when the true deep bodytemperature Tcore is constant (in the experiment, the rectal temperatureis simultaneously observed for verification).

This fluctuation is caused by the deviation in the in vivo thermalresistance Rthbody and the changes in the environmental temperature. Inactual practice, it is unclear whether or not the true body temperatureTcore is constant. However, in a period during when the deep bodytemperature Tcore is unlikely to be changed so much, for example, in acase where a rapid change in the environmental temperature (a changewithin several minutes), as fast as the deep body temperature Tcore doesnot significantly change, is detected, the in vivo thermal resistanceRthbody is calculated at the timings A, B as described above.

When the user is exercising, a sudden change in the body temperature mayoccur. Thus it is preferable to execute a step of obtaining the in vivothermal resistance Rthbody when a heart rate is equal to or less than athreshold value, as shown in FIG. 18(b).

When the in vivo thermal resistance Rthbody is calculated at the timingsA, B, differential waveforms of the deep body temperatures Tcore at thetimings A, B may be observed to carry out the calculation, as indicatedby a dotted line of FIG. 18(a).

Even in a case where the true deep body temperature Tcore graduallychanges, the gentle change can be offset by using the differentialwaveform, so that the change from the offset can be easily determined.For the differential waveform, a high-order differentiation, i.e. atleast the second order differentiation may be used.

For example, the in vivo thermal resistance Rthbody is calculated at atiming when the environmental temperature significantly changes duringthe user wears the biological data measurement device for a day, and thein vivo thermal resistance Rthbody is more accurately determined bycalculating in accordance to the reliability from several values of thein vivo thermal resistance Rthbody.

A method for requesting to the user to input a distance body_d from abody core to epidermis will be described with reference to FIG. 19(a) asa fourteenth embodiment.

According to the fourteenth embodiment, the user is requested to inputan in vivo body core distance body_d, which is a distance from the bodycore to the epidermis (body surface), as an alternative when a propervalue of the in vivo thermal resistance Rthbody cannot be obtained inthe eleventh embodiment stated above (the method for obtaining the invivo thermal resistance Rthbody from the transient response uponwearing).

The in vivo thermal resistance Rthbody can be obtained by multiplyingthe in vivo body core distance body_d by the thermal resistivity fromthe body core to the epidermis. As a method for the user to know the invivo body core distance body_d, it is possible to obtain a temporary invivo thermal resistance Rthbody based on a measured region andstatistical data by inputting height and weight, in addition to a methodusing the GSR. As described above, the in vivo thermal resistanceRthbody can be updated to a more accurate value during the measurementas appropriate.

As another method, the body temperature at rest is input and received,and the in vivo thermal resistance Rthbody is calculated back from thesubstrate temperature Tsub and the body surface temperature Tsk, both ofwhich are obtained at an initial stage of the measurement, so that thedeep body temperature Tcore coincides with the received temperature,instead of requesting the user to input the in vivo body core distancebody_d.

The rectal temperature at rest is 37·C·0.2·C, of which individualdifference is small. Since the abdominal temperature falls within arange of about 0.5·C with respect to the rectal temperature, a valuearound 37·C can be used as an initial value when the temperature at restcannot be input.

A posture correction based on acceleration will be described withrespect to FIG. 19B as a fifteenth embodiment. In this case, thebiological data measurement device 1 is provided with an accelerometer(acceleration sensor), as will be described later.

Since the in vivo body core distance body_d may change depending on theuser's posture (for example, standing posture and lying posture), theinfluence of the posture can be reduced using a value of accelerationobtained by the accelerometer.

When Az is acceleration in a direction perpendicular to the body surfaceof the user (Az is 0 when the user is sitting or standing, and Az is 1Gwhen the user is in a supine position [G is a gravitationalacceleration]), the corrected in vivo body core distance body_d2 fromthe body core to the body surface is obtained from the equationbody_d−a×Az, in which a is a coefficient and acquired from experimentsor the like.

The in vivo thermal resistance Rthbody is calculated using the correctedin vivo body core distance body_d2 to acquire the deep body temperatureTcore. Furthermore, the convection of the air layer A in the case 100varies depending on a direction with respect to the gravitationalacceleration to fluctuate a heat conductivity of the air layer A, whichmay cause a problem. Also in this case, the present inventionencompasses that the thickness and the thermal resistance of the airlayer A are corrected using the acceleration such as Az.

Additionally, the air layer A in the case 100 slightly changes dependingon the environmental conditions such as atmospheric pressure, humidity,etc. Therefore, it is possible to correct the air layer using theatmospheric pressure or the humidity, measured at the same time, inresponse to a target accuracy of the body temperature measurement.

The biological data measurement device 1 can be calibrated using a hotplate, a constant temperature bath, or the like. The infraredthermometer 21 is placed on the hot plate assuming that the hot plate isthe skin, and the environmental temperature is varied in the constanttemperature bath. The thermal resistance of the air layer is obtainedfrom the calibration.

The algorithm used in the present invention can be executed by thecontrol circuit 314 installed in the biological data measurement device1, or can be executed at a server on the cloud.

The ECG measurement circuit 310, the GSR measurement circuit 311′, andthe GSR driving circuit 312′, which are installed in the biological datameasurement device 1, will be described with reference to FIGS. 20 to 22, as a sixteenth embodiment.

Each of the ECG measurement circuit 310 and the GSR driving circuit 312′includes a low-pass filter (LPF), and the GSR measurement circuit 311′includes a high-pass filter (HPF). The cutoff frequencies are set tof_(ECG, LPF)<f_(GSF HPF)·f_(GSR, LPF).

The GSR measurement circuit 311′ further includes an A/D converter forperforming undersampling of fs, a bandpass filter (BPF) for passing|fc−N·fs| (N is an integer), and an integrator of T=1/|fc−N·fs|.

The biological data measurement device 1 is attached onto the skin (bodysurface) and measures the deep body temperature Tcore and the like for along time. Thus, the heat generation needs to be extremely suppressed,and different approaches are required to reduce the power consumption.The basic frameworks realizing lower consumption using passive elements,lowering a sampling frequency to the limit, and signal processing withlower calculation amount.

An ECG signal frequency in the ECG measurement circuit 310 is several Hzto several tens Hz, and is set to, for example, several tens Hz toseveral hundred Hz as f_(ECG, LPF), so that this signal frequencypasses. The LPF removes a GSR driving signal set on a high frequencyside. Since the ECG signal has a relatively wide band at 100 Hz or less,the A/D converter (ADC) executes Nyquist sampling while setting thesampling frequency to several tens Hz to several hundred Hz.

The GSR driving frequency fc in the GSR driving circuit 312′ is set toseveral hundred Hz to several tens kHz avoiding the ECG signalfrequency. It is set to, for example, several hundred Hz to several tenskHz as f_(GSR, HPF) to remove 1/f noise and thermal noise.

In the GSR sampling, the A/D converter (ADC) performs the undersamplingoperation and sets as a sampling frequency fs to, for example, around 1kHz. Although the sampling frequency is relatively high, intermittentoperation is performed in a specific time window to reduce the powerconsumption. A time window avoiding a periphery of the R wave, which isa main peak timing of the ECG, is set as the specific time window,whereby it hardly influence the R wave measurement with time intervals.

The GSR signal appears at a frequency of |fc−N·fs|(N is an integer) byundersampling. For example, when fs is set to 1024 Hz and fc is set to5028 Hz, the GSR signal appears at 32 Hz. 1/f noise, thermal noise andquantization noise are eliminated by narrowing a bandwidth to pass 32 Hzas a digital BPF.

Furthermore, by integrating the power of the signal (the square of thesignal) with respect to the time of M/32 sec, a first null point appearsat 32 Hz when, for example, M is 1. A carrier frequency of the GSRdriving is set to match with a frequency of the null point, and thus itis possible to remove a carrier component with an extremely lowcalculation amount and to extract amplitude information whichcorresponds to the changes in the skin resistance.

The GSR phase information may be necessary in some cases when obtainingthe in vivo body core distance body_d from the body core to theepidermis (body surface). The GSR driving signal passes subcutaneous fatand causes a certain phase shift. A thickness of the subcutaneous fatcan be estimated by observing an amplitude at where the phase isshifted. The integration starts from the certain phase of the GSRdriving signal in order to observe an amplitude at a specific phase ofthe GSR driving signal, thus it is possible to easily extract theamplitude of the specific phase.

The GSR driving frequency fc is set to several hundred Hz to severaltens kHz. Additionally, the cutoff frequency f_(GSR, LPF) of the LPF ofthe GSR driving circuit 312′ are set to several hundred Hz to severaltens kHz so that the GSR driving frequency fc passes and a highfrequency is attenuated.

A seventeenth embodiment of the present invention will be described withreference to FIGS. 23 and 24 . In the ninth embodiment as previouslystated, when the biological data measurement device 1 is attached to theliving organism, the case 100 is pressed against the body surface by thewearing belt 200. Meanwhile, in the seventeenth embodiment, the case 100is placed on the wearing belt 200 and attached to the living organism.

The seventeenth embodiment employs a four-electrode method. As shown inFIG. 24 , four electrodes 211, 212, 213, 214 are provided on a surface(rear surface) of the wearing belt 200, which is in contact with thebody surface. Portions other than the electrodes 211, 212, 213, 214 arecovered with an electrical insulating sheet 230 on the rear surface ofthe wearing belt 200.

Referring to FIG. 14(b), two inner electrodes 211, 212 are connected tothe ECG measurement circuit 310 and the GSR measurement circuit 311′ viathe contact portions C1, C2, while two outer electrodes 213, 214 areconnected to the GSR driving circuit 312′ via the contact portions C3,C4.

The male contacts 221, 222, 223, 224, which respectively constitute thecontact portions C1, C2, C3, C4, are provided on a surface (a back sideof the paper in FIG. 24 ) of the wearing belt 200.

The electrode 211 is connected to the male contact 221 via a lead wiring211 a. The electrode 212 is connected to the male contact 222 via a leadwiring 212 a. The electrode 213 is connected to the male contact 223 viaa lead wiring 213 a. The electrode 214 is connected to the male contact224 via a lead wiring 214 a.

In the seventeenth embodiment, the bottom surface of the case 100 isopen, as shown in FIG. 23(a). A case/wearing belt connecting substrate131 is provided in the case 100, in addition to the substrate 10.

Although not shown in detail, the thermometer including the infraredthermometer 21, the transmitter 24, the signal processing circuitcluster 300 (described above) and the like are installed on thesubstrate 10.

The case/wearing belt connecting substrate 131 is disposed on the bottomsurface side further than the substrate 10, and has an opening at acenter portion thereof, in order to prepare a field of view of theinfrared thermometer 21 and the air layer A. The case/wearing beltconnecting substrate 131 of the substrate 10 is provided in the case 100via the cylindrical support member 30 made of the heat insulatingmaterial. Furthermore, according to the seventeenth embodiment, a casethermometer 331 is provided on an inner surface of the upper lid of thecase 100.

Referring also to FIG. 23(b), the female contacts 111 to 114,respectively constituting the contact portions C1 to C4, are provided atfour corners of a bottom surface of the case/wearing belt connectingsubstrate 131, as engaging sides of the male contacts 221 to 224 on aside of the wearing belt 200. These female contacts 111 to 114 areconnected to, via the wiring, the ECG measurement circuit 310, the GSRmeasurement circuit 311′, the GSR driving circuit 312′ and the like,which are installed on the substrate 10.

In the seventeenth embodiment, the conductive magnets are adopted in themale contacts 221 to 224 and the female contacts 111 to 114, thusone-touch electrical-mechanical connection can be established.

Since the case 100 is placed on a surface side of the wearing belt 200,the infrared thermometer 21 measure a surface temperature of the wearingbelt 200. Thus, in the seventeenth embodiment, the deep body temperatureTcore is calculated by adding the thermal resistance Rth of the wearingbelt 200 to the thermal resistance Rth of the skin.

The surface of the wearing belt, of which temperature is measured by theinfrared thermometer 21, is preferably made of a material having aninfrared emissivity close to 1. As another example, the body surfacetemperature may be directly measured by removing the wearing belt at aportion corresponding to a solid angle of the infrared thermometer 21.

An aspect in which the case 100 of the biological data measurementdevice 1 is coupled with the wearing belt 200 by a detachable hook willbe described with reference to FIGS. 25(a) to 25(c), as an eighteenthembodiment of the present invention.

In the eighteenth embodiment, the case 100 is electrically andmechanically connected to the wearing belt 200 with hooks F1 to F4,instead of the contact portions C1 to C4 in the seventeenth embodiment.Each of the hooks F1 to F4 includes a combination of a female member 141having an opening and a hook-shaped male member 241, as illustrated inFIG. 25(c).

Accordingly, in the eighteenth embodiment, the case/wearing beltconnecting substrate 131 has a size to protrude from the case 100, andthe female members 141 of the hooks F1 to F4 are provided at fourcorners thereof. On the other hand, the male members 241 of the hooks F1to F4 are provided on the side of the wearing belt 200.

Both of the female member 141 and the male member 241 are made of aconductive material. The electrical-mechanical connection is establishedwhen the male member 241 is hooked on the female member 141. The malemember 241 may be provided on a side of the case 100, and the femalemember 141 may be provided on the side of the wearing belt 200.

The positions of the hooks F1 to F4 correspond to the contact portionsC1 to C4 in the seventeenth embodiment, respectively. Two innerelectrodes 211, 212 are connected to the ECG measurement circuit 310 andthe GSR measurement circuit 311′ via the hooks F1, F2, while two outerelectrodes 213, 214 are connected to the GSR driving circuit 312′ viathe hooks F3, F4.

Since the eighteenth embodiment adopts the four-electrode method, thehooks are arranged as two pairs on right and left sides. However, in acase where the two-electrode method is employed, it is enough that thehooks are arranged as one pair on right and left sides. Regardless ofwhich configuration is adopted, the case 100 is easily attached to ordetached from the wearing belt 200 according to the eighteenthembodiment. Thus, it is extremely convenient when, for example, charginga built-in battery or choosing a wearing belt.

An aspect in which the biological data measurement device 1 is installedon the single substrate 10 will be described with reference to FIG. 26 ,as a nineteenth embodiment of the present invention.

As described above, the biological data measurement device 1 is providedwith the signal processing circuit cluster 300 including the ECGmeasurement circuit 310, the GSR measurement circuit 311′, the GSRdriving circuit 312′, the communication circuit 313′, the controlcircuit 314, and the memory circuit 315. In the nineteenth embodiment,each of these circuits is modularized and installed on the substrate 10.

SiP (system-in-package) can be used as a module. It is possible to mountan antenna (transmitter 24), a communication chip, a microcomputer (MPU)chip, a memory chip and the like within a single module.

In the nineteenth embodiment, the substrate 10 is further provided withan accelerometer 321, a hygrometer 322, a microphone 323, and abarometer 324. The infrared thermometer 21 is disposed on a rear surfaceside of the substrate 10 as a heat flow meter.

The microphone 323 can be used for auscultation of the chest and theabdomen. Furthermore, the microphone 323 is capable of picking upenvironmental sounds to determine contexts relevant to walking,vehicles, works, conference, meal, toilet, sleeping and the like.Alternatively, a voice command may be input using the microphone 323.

The biometric data collected by the biological data measurement device 1can be sent to a mobile terminal B and processed by a CPU installed inthe mobile terminal B. Furthermore, data can be sent from the mobileterminal B to a server C and processed by the server C. The processingresults can be displayed on a screen of the mobile terminal B.

In accordance with the processing result, a control command may be sentto the biological data measurement device 1 in order to change thebiological data acquisition conditions. The vital signs can be read bythe voice instead of displaying on the screen.

For example, in a case where the user instructs to read the deep bodytemperature every 0.5·C via a microphone of the mobile terminal B, thedata flow is as follows.

Flow of command information: 1) speech recognition on the mobileterminal B, 2) acceptance and reply of the command on the server C, and3) reading the replay on the mobile terminal B.

Data flow: 1) heat flow data obtained by the infrared thermometer, 2)calculation of the deep body temperature Tcore on the mobile terminal,3) determination of 0.5·C fluctuation, and sending read data when thecondition is satisfied, on the server C, and 4) reading the data on themobile terminal B.

Furthermore, the present invention can also be used for countermeasuresagainst metabolic syndrome. According to the present invention, thedistance body_d from the body core to the epidermis, which is unknown,is automatically obtained, thus it is possible to show to the user thedecrease in the subcutaneous fat caused by the exercise.

Additionally, it is possible to show caloric expenditure due to aerobicexercise from temperature rise in the body core, heart rate,acceleration, etc., and thus the exercise effect can be enhanced.

The present invention can also be used for various biofeedbacktechniques (autonomous training, mindfulness, breath control, etc.). Thesensors (biological data measurement device) are attached to severalbody regions including limbs, thereby estimating a state ofvasodilatation from a peripheral core temperature, grasping a state ofautonomic nerves from electrocardiographic signal fluctuation, andfurther measuring a breathing rate from an amplitude of theelectrocardiographic signal and visualizing the breathing rate to theuser. Therefore, it is possible to enhance the effects of thebiofeedback techniques. Additionally, the terminal can be cooperatedwith the cloud in order to, for example, process, store, cite, share,and interpret by AI the data.

In the nineteenth embodiment, a single substrate is used as thesubstrate 10 on which the components are installed. However, as atwentieth embodiment of the present invention, the biological datameasurement device can be dividedly installed on two substrates, i.e. afirst substrate 10 a and a second substrate 10 b, as shown in FIG. 27 .

Both of the substrates 10 a, 10 b are rigid substrates. In the twentiethembodiment, the modularized signal processing circuit cluster 300, theaccelerometer 321, the hygrometer 322, the microphone 323 and thebarometer 324 are mainly installed on one substrate, i.e. the firstsubstrate 10 a. The power supply circuit 316 and the battery 317 areinstalled on the other substrate, i.e. the second substrate 10 b.

It is preferable that the substrates 10 a, 10 b have an area of about 10mm², and are connected by a flexible substrate 10 c so as to go along acurvature of the living organism. In this embodiment, the infraredthermometer 21 is installed as the heat flow meter on each of thesubstrates 10 a, 10 b. It is preferable that the flexible substrate 10 chas a high thermal resistance in order to reduce the thermalinterference between those heat flow meters.

Various exemplified configurations for an electrical-mechanical contactportion between the wearing belt 200 and the case 100 of the biologicaldata measurement device 1 will be described with reference to FIGS.28(a) to 28(e). In the following descriptions, a contact portion on theside of the case 100 is referred to as a first contact 110, and acontact portion on the side of the wearing belt 200 is referred to as asecond contact 220.

First, in a first example shown in FIG. 28(a), both of the first contact110 on the side of the case 100 and the second contact 220 on the sideof the wearing belt 200 are conductive magnets. The conductive magnet isgenerally disk-shaped, such as a coin or a button; or alternatively, itmay be a square. In a case where both the first contact 110 and thesecond contact 220 are the same magnets, there is an advantageous effectthat center positions of the magnets are automatically aligned(matched).

The conductive magnet of the second contact 220 is electrically andmechanically connected to the electrode 210 (211 to 214) made of aconductive pattern, with a conductive adhesive, on the side of thewearing belt 200. It is possible to reduce a contact potential with theskin by using a material of which main component is silver (Ag) orsilver chloride (AgCl) in the conductive pattern.

In a second example shown in FIG. 28(b), the first contact 110 on theside of the case 100 is a conductive magnet, while the second contact220 on the side of the wearing belt 200 is a magnetic element havingmagnetism, such as iron. In this case, it is preferable to provide arecess 220 a, into which the first contact 110 is fitted, on the secondcontact 220.

The magnetic element of the second contact 220 may be electrically andmechanically connected to the electrode 210 made of the conductivepattern, with the conductive adhesive, as in the first example.Alternatively, the magnetic element of the second contact 220 may besubjected to silver plating, and terminal fusion bonding may beperformed between the silver-plated magnetic element and the silverincluded in the conductive pattern of the electrode 210.

A third example shown in FIG. 28(c) is a modified example of the firstexample, in which the electrode 210 is formed by the conductive pattern,and then the conductive magnet used as the second contact 220 is fixedby a gate-shaped caulking needle 220 b. The second contact 220 iscovered with an electrical insulating sheet 230 after caulking.

A fourth example shown in FIG. 28(d) is a modified example of the secondexample, in which a caulking leg 220 c is formed on the magnetic elementitself used as the second contact 220, and then the caulking leg 220 cis embedded into the electrode 210 to fix the second contact 220. Alsoin this case, the second contact 220 is covered with the electricalinsulating sheet 230 after caulking.

A fifth example shown in FIG. 28(e) is that the conductive magnetic usedas the second contact 220 is disposed on the electrode 210 (below theelectrode 210 in FIG. 28(e)) on the rear surface of the wearing belt200, and the conductive magnetic is fixed onto the electrode 210 bypunching a gate-shape caulking fitting 220 d in the electrode 210 andthe wearing belt 200 from the surface side of the wearing belt 200.

According to the fifth example, the case 100 of the biological datameasurement device 1 is disposed on the rear surface side of the wearingbelt 200, and pressed against and mounted onto the body surface by thewearing belt 200, as shown in FIG. 13(a) of the ninth embodiment.

Although the present invention has been described with reference to eachof the embodiments stated above, the present invention is not limitedthereto. Techniques, equivalents and the like, derived from each of theembodiments, are also encompassed in the scope of the present invention.

The invention claimed is:
 1. A biological data measurement device inwhich a living organism having a first thermal resistance from a core toa surface is a measuring object, the device comprising: a heatinsulating layer which is disposed on the surface of the measuringobject and has a second thermal resistance; measurement means formeasuring a first and a second temperature segregated by the heatinsulating layer; and adding means for adding a predetermined delay timeto the second temperature in order to correct a response delay of thefirst temperature as compared with the second temperature, wherein thefirst temperature is a bottom side temperature of a bottom surface ofthe heat insulating layer, which is in contact with the surface, and thesecond temperature is a top side temperature of a top surface of theheat insulating layer.